Enhanced bonding layers on native oxide surfaces

ABSTRACT

An implantable device with a metal, metal alloy, metalloid, polymeric or ceramic surface and a phosphonic acid coating layer directly contacting the surface wherein the surface has hydroxyl groups covalently bonded to the acid groups of the coating layer and the phosphonate organic ligands are omega-functionalized.

CROSS REFERENCE TO RELATED APPLICATIONS

The present application is a continuation-in-part of U.S. application Ser. No. 10/179,743, filed Jun. 24, 2002, which application claims the priority of U.S. Provisional Application Ser. No. 60/300,144, now abandoned, filed Jun. 22, 2001, and which application in turn also is a Continuation-In-Part of U.S. application Ser. No. 09/668,080, now U.S. Pat. No. 6,645,644, filed Sep. 22, 2000, which application, in turn, claims priority from U.S. Provisional Patent Application Ser. No. 60/155,398, now abandoned, filed Sep. 22, 1999. The disclosures of all applications described above are incorporated herein by reference.

FIELD OF THE INVENTION

The present invention relates to coatings bonded to the oxide surface of titanium metal and titanium alloys (collectively, titanium materials) by treatment of the oxide surface with phosphorous-based acids. The present invention further relates to coating layers which increase the adhesion strength between a coating and a substitute. The present invention further relates to implantable medical devices fabricated from titanium materials having bonded coatings which impart an osteoconductive surface to the medical device. In addition, the present invention relates to methods for forming such coatings on the surface of implantable medical devices to provide an osteoconductive surface, and methods for using implantable devices bearing an osteoconductive surface.

BACKGROUND ART

Titanium metal combines the strength of steel with the light weight of aluminum, and for this reason the metal and its alloys are used extensively in the aerospace and aviation and high performance sports equipment industries. Titanium metal and its alloys (hereinafter, “titanium materials”) are also resistant to corrosion under ambient conditions. Because of its mechanical properties and chemical resistance to degradation by bodily fluids, titanium materials are used extensively to fashion metal fitments used as dental and orthopedic implants (medical implants). When a metal fitment is used as a medical implant, it is important to create a stable bond between bone tissue and the surface of the implant. Poor bonding at the interface between the surface of the implant and the bone tissue leads to low mechanical strength of the bone-to-implant junction and the possibility of subsequent implant failure. An important goal for interface optimization is to use species which are biocompatible and which enable bone mineralization at the interface following implantation. Bone tissue is a combination of protein and mineral content, with the mineral content being in the form of hydroxyapatite. Currently, there is no effective way to obtain strong attachment of incipient bone with the implant material at the interface between the surfaces of the two materials in order to “stabilize” the implant.

The problem of synthesizing an adhesion-promoting interface on implants is often approached from the prospective of high temperature methods, including using plasma or laser-induced coating techniques. However, these methods engender problems of implant heating and surface coverage. For example, calcium phosphate deposition at high temperatures can give rise to ion migration. Plasma-induced phosphate coating of a titanium substrate gives surface hydroxyapatite as well as surface calcium phosphate, titanates and zirconates. Therefore, control of surface stoichiometry can be problematic, and defects at the interface may translate into poor mechanical strength.

The use of intermediate layers, for example of zirconium dioxide, to enhance hydroxyapatite adhesion and interface mechanical strength has been explored with success. However, a practical limitation involving laser or plasma deposition is that it is hard to obtain comprehensive coverage on a titanium implant of complex 3-dimensional structure. The zirconium dioxide interface formed at high temperatures is of low surface area and maintains few, if any, reactive functional groups for further surface modification chemistry. A silicate, phosphate or phosphonate interface can function to nucleate the growth of hydroxyapatite, thereby minimizing implant failure and the attendant need for serial revision implant surgery, which can be a consequence of unstable implant-to-bone interaction, but, as described below, there is little success of providing such surfaces on the oxide surfaces of titanium materials.

Solution-phase surface processing does not suffer from the practical limitations of surface coverage that can be attendant with plasma or laser-based deposition methods, and procedures involving formation of hydroxyapatite from solution, often using sol-gel type processing, have been accomplished. Elegant methodologies have been developed in which graded interfaces have been prepared, extending from the pure implant metal to the biomaterial at the outer extremity by way of silicates. However, while solution-based procedures are inexpensive and give rise to materials resistant to dissolution by bodily fluids, adhesion of the hydroxyapatite to the implant metal is less strong than is observed when deposition is accomplished by plasma spraying techniques.

The deficiency of these solution approaches may lie in the nature of the native oxide surface of titanium materials. Exposure of a clean surface of titanium materials to oxygen results in the spontaneous formation of surface titanium oxides (native oxide). The exact chemical stoichiometry and structure of these oxides varies from material to material, and with depth in the oxide layer, with environmental variables, and with the processing history of the material. The oxide layer may be stoichiometric, super-stoichiometric, or sub-stoichiometric with respect to TiO₂, a stable oxide of titanium. Generally, the uppermost layer of the native oxides comprises some form of TiO₂. It may be crystalline, but if crystalline, it is generally disordered. Typically, many different phases exist within the oxide layer between the metal and the ambient environment. Generally, the uppermost layer of oxide includes widely dispersed hydroxyl functional groups bonded to a titanium atom. The surface forms spontaneously by exposing the metal or alloy to the ambient environment, and is alternatively described as the “native oxide surface” of a titanium material.

The inert nature of a native titanium oxide surface, even with regard to bonding with typical adhesives, is known and has been studied, for example, by Srivastava as reported in the International Journal of Adhesion and Adhesives, 23 (2003) pgs. 59-67. In this study, a film of an adhesive composition, for example, an epoxy-based adhesive applied to the freshly cleaned surface of a Ti-6Al-4V titanium alloy coupon was observed to oxidatively degrade at the metal/native oxide/proxy coating interface resulting in a reduction of adhesive strength between the metal and the adhesive coating.

This oxide layer protects the underlying material from further chemical attack in that it is generally resistant to further chemical reaction. This property of the oxide surface of titanium materials mitigates against the adhesion of other moieties to it, for example, coatings and bone tissue, making application of an adhesion-promoting coating to the native oxide surface problematic. For example, a phosphorous-based acid incorporating into its structure an organic moiety, for example organo-phosphonic acid, does not readily form an adherent coating with the bulk metal under ambient conditions. This is in contrast to other metals that possess oxide coatings, for example, tin, iron, aluminum and copper, or their alloys, for example, steel, or bulk oxides, for example, mica, all of which yield an adherent film when treated with such acids. Film formation of the type observed between, for example, zirconium surface oxides and organophosphonic acids, is not observed with the oxide surface of titanium materials. An example of this is described by Gao et al. in Langmuir, Vol. 12 (1996) p. 6429.

For many materials other than titanium, as described above, the native oxide surface can be altered chemically (derivatized) by exposing the surface to various hydrolytically reactive reagents. An example of derivatizing an oxide surface in this manner is exposure of the surface of a silicate (silicon oxide) to a trimethylsilyl derivative which “silanates ” the surface, converting it from a hydrophilic surface to one that is hydrophobic by bonding trimethyl silyl functional groups to the native oxide surface. Typically, chemically derivatizing a surface is the most cost-effective method to achieve uniform surface coverage on surfaces having complex shapes, and in general represents the least impact to the mechanical properties of the material derivatized compared to other surface modification techniques.

Silanization has long been considered the benchmark method for attaching organics to titanium and its alloys, for example, Ti-6Al-4V, via their native oxide coatings. Direct silane-surface bonding is limited by surface hydroxyl group content, and the OH group content of the Ti native oxide surface is low, accounting for only about 15% of total surface oxygen. Low yields of direct surface silanization result, and silane reagent crosslinking can be the dominant mode of reactivity. Unfortunately, surface-bound and cross-linked siloxanes can be hydrolytically unstable, which can further reduce amounts of key organics that are coupled to simple surface silanization reagents under aqueous conditions.

It will be appreciated that for metal oxide surfaces which are not derived from titanium metal or its alloys, for example, the oxide surface of aluminum and its alloys or the oxide surface of silicon, it is common to carry out reactions between organometallic complexes and hydroxyl groups terminating the oxide layer to provide for a surface which is amenable to further derivatization or passivation. For these “non-titanium material” oxide surfaces, in cases in which the natural occurrence of hydroxyl groups per unit area of surface is too sparse to provide for the formation of a dense surface layer of the derivatization products, it is known to subject the oxide surface to a variety of hydrothermal treatment schemes to increase the density of hydroxyl sites and improve the reactivity of the surface toward derivatization. It will also be appreciated that the methods and coating layers of the present invention, described below for titanium native oxide surfaces can be equally well applied to the native oxide surfaces of other materials.

In general, the coverage of naturally occurring hydroxyl sites which form on titanium material oxide surfaces is too sparse to provide dense-coverage layers of derivatization product on the surface of the material by traditional derivatization routes. Additionally, attempts to increase the actual density (sites/unit area) of hydroxyl sites on the surface oxides of titanium materials results in “roughening” of the surface, which, while increasing the number of hydroxyl sites on the projected (nominal) surface area of the bulk material, also increases the actual surface area of the material, and, consequently the density of hydroxyl sites/unit area remains approximately constant.

If the protective oxide layer of a titanium material is dissolved under conditions in which its re-formation is inhibited, rapid corrosion of the material will occur, an example of which is reported by Fang et al. in Corrosion, Vol. 47, (1991), p169. Reducing acids, for example hydrobromic, sulfuric, and phosphoric acid, under the proper conditions of heat and acid concentration, can attack titanium metal and its alloys. Such attack is especially facile when oxidizing agents, for example, air, are excluded from the surface of the material under attack. For example, titanium metal rapidly dissolves in 85% phosphoric acid at 80-100° C. yielding a solution from which titanium(III) dihydrogen orthophosphate (Ti[H₂PO₄]₃), (hereinafter, “Ti-phosphate”) can be isolated.

A need exists for a methodology that combines the benefits such as those obtained from the physical deposition of interfacial zirconium dioxide with the coverage, processing and speciation control of solution-based methods described above. Additionally, a need exist for a methodology that makes the oxide surface of titanium materials amenable to solution process derivatization that establishes dense-coverage, robust and adherent coatings amenable to establishing a strong interface between the oxide surface and materials with which the surface is placed in contact, for example, the provision of a surface which exhibits strong bonding to an adhesive film applied to it, the promotion of adhesion between medical implants made of titanium materials and the tissues into which they are implanted, and the provision of a surface which promotes bone integration into the implant/tissue interface.

SUMMARY OF THE INVENTION

It has now been discovered that heating a self-assembled layer of an omega-functionalized phosponic acid on the native oxide surface of a substrate will form an adherent coating layer that may be further derivatized with adherent species. Therefore, according to one aspect of the present invention there is provided on the native oxide surface of a material a multi-segmented, phosphorous-based coating layer having a difunctional organo-phosphonic acid-based segment bonded to the native oxide surface of said material and a linking segment bonded to said organo-phosphonic acid-based segment.

Accordingly, the present invention also provides a phosphorous-based coating layer comprising a plurality of omega-functionalized organo-phosphonate moieties bonded to the native oxide surface of a substrate by a phosphonate bond and a plurality of one or more coating moieties selected from the group consisting of inorganic, organic, or bioactive moieties, each said coating moiety being bonded to the omega-functional group of at least one omega-functionalized organo-phosphonate moiety by means of a member of the group comprising a metal complex and an organic polymer, and when bonded by means of a metal complex, the metal complex further characterized by being derived from a metal reagent, preferably a metal alkoxide reagent, and when bonded by means of an organic polymer, the organic polymer further characterized by being derived from an ionic or step-reaction polymerization which incorporates one or more of said omega-functional groups into said polymer.

Preferred native oxide surfaces are the surfaces of titanium metal and its alloys. It is preferred for the organo-phosphonic acid-based segment to be derived from an omega-functionalized organo-phosphonic acid containing a hydrocarbon ligand having from about 2 to about 40 carbon atoms, wherein the hydrocarbon ligand is a linear or branched, saturated or unsaturated, substituted or unsubstituted, aliphatic or aromatic alkylene moiety.

Another aspect of the present invention is a process for the provision of an adherent, phosphorous-based coating layer having a difunctional organo-phosphonic acid-based segment bonded to the native oxide surface of said material and a coating bonded to said organo-phosphonic acid-based segment, the process comprising: (i) providing a native oxide surface bearing an omega-functionalized organo-phosphonic acid moiety bonded thereto; (ii) and bonding said omega-functional groups thereof, or derivatives of the functional groups thereof, with a bioactive, organic, or inorganic moiety comprising the coating. Preferred omega-functional groups are hydroxyl-,carboxylate-, amino-, thiol-, and phosphonato-functional groups, or these groups further derivatized by reaction with a metal or organo-metal reagent, for example an alkoxide. These groups participate in further bonding with moieties comprising the organic, inorganic, or bioactive coating layer, either through strong chemical bonding, for example, covalent bonding, or through weaker bonding interactions, for example, hydrogen bonding.

Preferred metal reagents for derivatizing omega-functional groups are, for example metal alkoxides, for example zirconium tetrakis(t-butoxide), silicon tetrakis(t-butoxide), titanium tetrakis (t-butoxide), and calcium bis(2-methoxy-ethoxide).

Preferred bioactive moieties are peptides which promote osteoblast adhesion, for example KRSR (lysine-arginine-serine-arginine) and derivatives thereof, for example KRSRGGC and KRSRGGE, and RGD (arginine-glycine-asp) and derivatives thereof, for example RGDC.

A preferred method of attaching a bioactive species to a native oxide surface comprises providing a phosphorous-based coating layer as described above wherein said said omega-functionalized organo-phosphonate moieties are an alkyl-bisphosphonate which has been derivatized with a metal alkoxide, and further reacted with an organic moiety, said organic moiety comprising a peptide bonded by a thiol-ether bond to a malimido-carboxylic acid group, said reaction providing a carboxylate bond to said metal alkoxide derivatized omega-functional group.

Additionally, organic moieties that may be added to the omega-functional group of a phosphonic acid-based layer which comprise oligomers or polymers, for example, adhesive polymers, for example epoxides, polymers which form surface coatings, for example acrylates, and oligomers, for example, those which have bioactive properties or which can be used to attach compounds or precursors to compounds having bioactive properties, for example, a polylactide-co-glycolide which has antibiotic activity.

Inorganic coating layers which may be bonded are, for example, hydroxyapatite.

The present invention thus includes the methods by which the coated substrates of the present invention are formed. Therefore, in accordance with another embodiment of the present invention there is provided a method of bonding a layer of a phosphorous-based acid moiety to a titanium oxide surface comprising coating said oxide surface with a phosphorous-based acid moiety self-assembled layer and heating said coated oxide surface until said self-assembled layer is bonded thereto, the phosphorous-based acid moiety comprising the self-assembled layer being selected from the group consisting of phosphoric acid and organo-phosphonic acids.

Preferred coatings are those which have been formed from alkylene- and arylene-organo-phosphonic acids, including substituted alkylene and arylene-phosphonic acids. More preferred are substituted alkylene phosphonic acids with a reactive substituent omega to the phosphonic acid functional group. Preferred oxide surfaces are the native oxide surfaces of titanium materials. It is preferred for the phosphoric acid to be in the form of an aqueous solution having a pH more acidic than about pH 3.0.

In some embodiments the adherent, multi-segmented, phosphorous-based coating layers of the present invention promote interaction between the coated substrate and the environment in which the coated substrate is placed by using the coating layer to improve the interaction of the two. An example of this is using a coating layer of the present invention to promote the adhesion of bone tissue to a titanium substrate on which a coating of the present invention is placed. In other embodiments, a segment of the adherent, multisegmented, phosphorous-based coating layer comprises a moiety which has surface active properties, and thus itself interacts with another surface. An example of this is the increase in adhesive force observed between an adhesive and a titanium native oxide surface when the adhesive is included as a linking moiety in the coating layer of the present invention.

Thus, in addition to the coatings of the present invention and the methods by which they are formed, the present invention also provides methods for coating, for example, implantable medical devices having a titanium oxide surface for contacting to bone tissue and thereby promoting the interaction of bone tissue with the surface of the implantable device, coated implantable devices and implantation methods incorporating the coated devices.

Other features of the present invention will be pointed out in the following description and claims, which disclose, by way of example, the principles of the invention and the best methods which have been presently contemplated for carrying them out.

DETAILED DESCRIPTION OF THE PREFERRED EMBODIMENTS

The present invention provides a dense-coverage, adherent, phosphorous-based coating bonded to the native oxide surface of a titanium material. The present invention also provides modified phosphorous-based coatings that effectively bond a dense-coverage, adherent coating of chemical species to the native oxide surface of a titanium material. Thus, the present invention provides, under mild conditions, on a native oxide surface of a titanium material, a derivatized surface which modifies the chemical properties of the native oxide surface. The present invention also provides a method of producing those surfaces which may be adapted to provide an even coating of the derivatized surface over a complex shape.

The present invention also includes inorganic phosphate and organic phosphonate coatings that have been directly covalently bonded thereto. Inorganic phosphate coatings are prepared by coating nietal-containing and metal alloy-containing substrates with a concentration of phosphoric acid effective to form a stable film on the substrate surface without excessively dissolving the substrate. This can readily be determined by those of ordinary skill in the art without undue experimentation. Phosphoric acid having a concentration between about 1.4 and about 2.8 M is preferred. Phosphoric acid coatings are similarly directly applied to a hydroxide-bearing substrate. These embodiments of the present invention advantageously eliminate a complicated process step requiring protection of a transition metal alkoxide coating layer from ambient moisture prior to the vacuum deposition.

The substrate is then heated to a temperature between about 40 and about 140° C., with a temperature of about 900° C. being preferred. Phosphate and phosphonate ligands then directly covalently bond to the substrate. The phosphonic acid ligands also polymerize to form organopolyphosphonate covalently bonded coatings.

Like the transition metal phosphate monoester and polyphosphate coatings, the inorganic phosphate coatings are rich in free hydroxyl groups. Each coating layer may be further functionalized to promote covalent attachment to bone tissue proteins, or precursors thereof, for example, by using thiol compounds conventionally employed to promote adhesion between gold metal implants and bone tissue. The hydrocarbon ligands of the organopolyphosphonate coatings may likewise be functionalized at the omega carbon as described above for phosphonate ligand coatings to form covalent bonds with chemical precursors of bone tissue protein or with the bone tissue protein itself.

The method of the present invention may also be employed to prepare passivating transition metal oxide coatings having improved substrate adhesion. Such transition metal oxide coatings are obtained by reacting the organic ligand coatings of the present invention with a basic solution capable of hydrolyzing the transition metal ligand, such as a 0.001 N to about a 1.0 N solution of a caustic material such as NaOH, KOH, NH₄ OH, and the like. Lewis bases capable of hydrolyzing the organic ligands may also be used. The transition metal alkoxide coatings may also be directly converted to transition metal oxide coatings, without first forming an organic ligand coating, by thermolysis of the transition metal alkoxide coatings at temperatures above 300° K., preferably between about 400° K. and about 500° K.

The phosphate and phosphonate coatings of the present invention are advantageously employed to provide osteoconductive surfaces for dental and osteopathic implants tat exhibit improved adhesion at the bone tissue interface. The coatings can be applied to essentially any implant intended for bone or dental tissue contact fabricated from a material having a hydroxide-bearing surface at the intended bone or cental tissue interface. Implants made of titanium and alloys thereof may be employed, as well as aluminum or iron, and alloys thereof, and the like.

Plastic polymer and ceramic materials with hydroxyl group-modified surfaces at the bone tissue interface may also be employed.

Ligand replacement reactions in the coordination sphere of surface transition metal complexes also make it possible to attach bin-compatible or bin-active organic co-polymers to implant surfaces. The purposes range from implant lubrication or reduction of adhesion to he delivery of organic phase-soluble drugs at the implant-bone tissue interface.

Substrates suitable for use with the present invention include any metal or metalloid capable of forming an native oxide overlayer, and essentially any substrate capable of being provided with an oxide overlayer coating by conventional techniques. The substrate may be a metal, metal alloy or metalloid with an actual native oxide overlayer, or a metal alloy or metalloid having an oxide overlayer physically produce by well-known oxidative conditions such as exposure to air and/or moisture. Dental and orthopedic implant substrates include titanium and alloys thereof such as Ti-6A1-4V.

Phosphoric acid coatings are covalently bonded as phosphate monoesters of the transition metal. The phosphate ligands may be hydrolyzed to form inorganic transition metal polyphosphate coatings on the substrate surface. The phosphate and polyphasphate coatings are rich in hydroxyl groups that are available for further chemical modification.

The inorganic transition metal phosphate monoesters also serve as a template for first chemical, then biological growth of bone tissue bydroxyapatite in the implant surface. Surface-bound inorganic transition metal phosphate monomeric units insinuate themselves directly into bone tissue hydroxyapatite to make a strong composite seal between the implant surface and the hydroxyapatite. Alternatively, the rnonoesters may be hydrolyzed to form inorganic transition metal polyphosphates having a two-dimensional structure, th.e monomeric units of which also insinuate themselves directly into bone tissue hydroxyapatite.

While the present invention can provide derivatized surfaces on the native oxide of any material, it is anticipated that the present invention will be most useful in the provision of derivatized surfaces of titanium metal or metal alloy native oxide. It is anticipated that most useful will be the provision of titanium alloy surfaces which promote increased bond strength between the derivatized surface and bone tissue, for example, the surface of a medical implant and interpenetration of bone tissue into the interface of the implant. Thus the present invention also provides a derivatized surface that promotes the adhesion and proliferation of osteoblasts, and provides a method of synthesizing such a surface. This aspect of the present invention is particularly useful for securely bonding replacement joints to bone tissue, for example, knee and hip replacements. Therefore, in addition to the coatings of the present invention and the methods for forming the coatings, the present invention provides a coating for implantable medical devices, methods for improving the adhesion to bone tissue of implantable medical devices, and methods for implanting medical devices by first coating them according to the present invention.

The coatings of the present invention are more amenable to chemical interaction with other chemical species than the native oxide surface upon which they are formed, but the underlying material (substrate) retains some of the native oxide surface, and thus the degradation-resistant properties of the native oxide surface. It will be appreciated that the coatings of the present invention may be formed as well on the native oxide surfaces of materials other than titanium materials, and will be equally effective in providing a surface having dense-coverage by moieties which are amenable to the further derivatization reactions, for example, those described below.

The phosphorous-based coating of the present invention is a dense-coverage, adherent phosphate or phosphonate layer bonded to the native oxide surface of a substrate of titanium material. As described above, these layers can promote adhesion between the titanium material and an applied chemical species, for example, when applied to a medical implant which is then contacted to living bone tissue, the layer can promote adhesion between the implant upon which such surface layers are formed and bone tissue. The present invention also provides a dense-coverage, adherent, derivatized surface on the oxide coating of a titanium material which is amenable to further derivatizing reactions that utilize hydrolytically reactive reagents to thereby provide a dense, adherent surface coating of these derivatizing species.

The methods of producing the phosphorous-based coatings of the present invention are not critical. It will be appreciated that many variations may be employed. In general, the surface to be coated is contacted with a phosphorous-based acid solution, the solvent removed, and the surface to be coated is then heated and held at temperature for a period of time while reaction between the phosphorous-based acid and the oxide surface proceeds.

In a typical coating procedure, the surface to be coated is prepared by sanding the surface clean, rinsing the sanded surface with solvent, for example, methanol, methylene chloride, and methyl-ethyl ketone, and drying the surface under conditions which preclude physisorbed water, for example, at 200° C. in the ambient environment.

Next, the surface is exposed to a phosphorous-based acid solution, and the solvent is allowed to evaporate, leaving a self-assembled film of phosphorous-based acid moieties on the surface.

Next, reaction between the film of phosphorous-based acid and the surface is initiated, for example, by heating the surface, for example, by placing the treated surface and substrate in an oven.

It will be appreciated that other methods of providing a coating of phosphorous-based acid on the oxide surface may also be employed, for example, by dipping the surface to be coated into a vessel containing the acid solution and draining the excess. A variation of this example is to dip the surface into a heated solution of the acid for a period of time which initiates reaction but does not substantially corrode the material, followed by annealing the material in an oven.

The coatings of the present invention are stable. Once formed, so long as fresh acid is not present, continued heating of the substrate and surface do not result in further reaction or degradation of the native oxide or phosphorous coating.

Typically, concentration of acid solutions will range from about 0.01 to about 30 millimolar (mM) of the acid species, although concentrations lying outside of this range may be used, for example, when the reaction rate of the phosphorous-based acid chosen is low.

The layer forms spontaneously and may be formed at any substrate temperature. Typically, it will be formed at temperatures between about 20° C. and about 200° C. to permit uniform application of the acid species to the surface oxide to be coated. Lower or higher temperatures may be required depending on time required to form a film and the concentration of acid species. Temperatures outside of this range may be employed where solubility and/or reactions rates of the chosen acid species do not preclude doing so.

The reaction forming the phosphorous-based coating of the present invention (also described as “annealing”) is typically carried out in the ambient environment because it is usually convenient to do so. It will be appreciated that it may also be carried out in inert environment, for example, in a vacuum oven or in an inert gas glove box.

Typically, the oxide surface is annealed at temperatures between about 100° C. and about 200° C. because the rate of film formation is reasonable at these temperatures and such an environment is accessible using simple ovens. Higher or lower temperatures may also be employed.

In general, it is convenient to drive the reaction using hot air heating of the surface, for example, using a drying oven, but methods of imparting energy to the surface, for example, radiant heating or laser radiation, may also be used.

It will be appreciated that numerous means may be employed to evaporate the solvent and to drive the reaction of the phosphorous-based acid with the surface that will also provide the phosphorous-based coatings of the present invention.

Substrates suitable for use with the present invention include any native oxide surface, for example, silicon, aluminum, and titanium. Titanium metal or titanium alloy (hereinafter, “titanium materials”) capable of forming a native oxide surface are especially preferred. As described above, implantable medical and dental devices (hereinafter, “medical implants”), are frequently made from titanium materials.

Titanium metal from which medical implants are made typically has a purity such that the mass of the material is greater than about 98 wt. % titanium, for example, the Allvac series of titanium metal available from Allegheny Technologies Company, for example, Allvac 70, which comprises about 98 wt. % titanium and Allvac 30 CP-1, which comprises 99.5 wt % titanium. Although the present invention is applicable to bulk titanium metal which is of either lower or higher purity, and such material is not outside of the scope of the present invention, in general the lower purity material is not employed as medical implant material.

Typical titanium alloys from which medical implants are made contain at least about 80 wt % titanium, with the remainder comprising other metals and trace elements. Examples of titanium alloys (titanium materials containing more than trace amounts of other metals) which are used in the construction of medical implants are also found in the Allvac series of titanium alloys available from Allegheny Technologies Company, for example, Allvac Ti-15-Mo, which contains about 15 wt. % Mo and in excess of about 84% titanium, Allvac 6-4, which contains about 4% vanadium, about 6 wt. % aluminum, and in excess of 89 wt % titanium (which alloy is also described herein as Ti-6Al-4V), and Allvac 6-2-4-Si, which contains about 6 wt % aluminum, about 2 wt % molybdenum, about 2 wt. % tin, about 4 wt. % zirconium, and in excess of 85 wt. % titanium. Other purities and specifications of titanium alloys, whether used for the construction of medical implants or not, are known, and are also amenable to the present invention, and are therefore also contemplated in the term “titanium materials”. It will be appreciated that materials which can be derivatized to have an oxide surface can also be employed.

For the application of phosphonate coatings using the general procedures described above, the phosphorous-based acid used is selected from the organic phosphonic acids. For purposes of the present invention, “phosphonic acid” refers to compounds having the formula H₂RPO₃, wherein R is an organic ligand with a carbon atom directly bonded to phosphorus.

Phosphonic acid species which are useful in the formation of coatings of the present invention may have, as the organic ligand of the molecule, a hydrocarbon which comprises an alkylene or arylene. Generally, useful alkylene and arylene hydrocarbon ligands will comprise between about 2 and about 40 carbon atoms, although the present invention contemplates organic portions outside of this range as the properties desired of the coating formed dictate larger or smaller organic portions.

An alkylene organic ligand of a phosphonic acid suitable for use in the present invention may be linear or branched, saturated or unsaturated, and unsubstituted or with one or more substituents. An arylene organic ligand may comprise direct attachment of an aromatic moiety to the phosphorous atom of the phosphonic group, or it may be attached by an intervening alkylene moiety. Additionally, the arylene ligand may be incorporated into an alkylene chain (an arylene moiety having two or more alkyl substituents) or be a substituent depending from an alkylene chain. Substituent from arylene moieties may additionally be unsubstituted or may have one or more additional substituents.

Substituents on the hydrocarbon portion of phosphonic acids useful in the present invention may be appended to any carbon atom of the hydrocarbon ligand. Useful substituents are, for example, reactive functional groups, for example, a hydroxyl group, carboxylic group, an amino group, a thiol group, a phosphonate group, and chemical derivatives thereof. It will be appreciated that any functional group which can participate in a further derivatization reaction can be employed. Additionally, an alkylene hydrocarbon ligand may contain within the structure or appended to the structure, reactive moieties, for example sites of unsaturation, which may be further reacted in a polymerization reaction with reactive substituents on the hydrocarbon ligands appended to other phosphonate sites bound to the surface of the native oxide during a phosphonate derivatizing reaction. In this manner, a phosphonate-organo-polymeric layer may be formed on the oxide surface. An example of such a polymerization reaction is the preparation of a surface coating of acrylic phosphonic acid. Unexpectedly, when acrylic acid and methacrylic acid substituents are employed, the polymerization proceeds spontaneously upon exposure to air. For less reactive coatings, the polymerization can be performed by exposing the coating to conventional polymerization reagents and conditions.

In a particularly preferred embodiment, coatings are formed from phosphonic acids having an organic ligand functionalized at the omega-carbon of the ligand which is further reacted to form covalent bonds with chemical precursors of bone tissue protein, such as amino acids, or with the bone tissue protein itself. For omega-functionalized phosphonic acids, the application of the acid to oxide surface generally results in a self-assembled phosphonic acid film with the omega-carbon directed away from the substrate surface and available for covalent bonding or further chemical modification. Preferred omega-functional groups include hydroxyl, amino, carboxylate, thiol, and phosphonate groups.

It will also be appreciated that the reactive substituents pendant on the organic portion of a phosphonate bound to the oxide surface can be further reacted with reagents which are subject to hydrolysis reactions. Examples include metal alkoxides, examples of which are those having the structure M(O—R)_(n), where M is a metal, R is a linear or branched, saturated or unsaturated, aliphatic or aromatic, substituted or unsubstituted hydrocarbon moiety, and “n” is equal to a stable valance state of the metal. Examples of metal alkoxide compounds are zirconium-tetrakis-(t-butoxide), titanium-tetrakis-(t-butoxide), and silicon-tetrakis-(t-butoxide) where R is a t-butyl group, M is respectively Zr, Ti, and Si, and “n” is four. It will be appreciated that other hydrolytically reactive compounds which have two or more alkoxide ligands in addition to other ligands may also be utilized. For example, calcium alkoxides, for example, calcium bis(2-methoxy-ethoxide). In general, alkoxide ligated metals in groups 2 through 14 will find utility in these secondary functionalization reactions with phosphonate coatings of the present development.

When the reactive moieties appended to the free ends of the phosphonate coating layer are deravitized with a metal alkoxide (this is to say, a metal alkoxide “linking” segments is added) substituents having organic pi-electron delocalized moieties may be appended to the linking segment by reaction with the metal. Essentially any pi-electron delocalized compound capable of reacting with a transition metal alkoxide to covalently bond a ligand of the moiety to the transition metal is suitable for use with the present invention. Particularly useful compounds are pi-electron delocalized aromatic ring compounds. A particularly preferred aromatic ring compound is a phenol, which has a relatively acidic hydrogen that is readily transferred to the transition metal alkoxide to initiate a reaction that results in the formation of a transition metal phenolate. Five-membered heteroaromatic ring compounds having proton-donating ring substituents capable of reacting with the transition metal alkoxide are also desirable because of their high degree of pi-electron delocalization. Examples of such rings include furan, thiophene and pyrrole.

Adherent, dense-coverage, phosphate coatings bound to the native oxide surface of a titanium material (hereinafter, “a coating of Ti-phosphate”) may be prepared by treatment of the surface under mild conditions with phosphoric acid according to the general procedure described above. For purposes of the present invention, “phosphoric acid” is defined according to its well-understood meaning, H₃PO₄. In the process of the present invention, treatment of a native oxide surface with phosphoric acid forms an inorganic phosphate coating that is rich in free hydroxyl groups. When the native oxide surface of a titanium material is coated with a phosphate coating of the present development and analyzed by XRD, two different titanium phosphate species were identified on its surface. One component, Ti₄H₁₁(PO₄)₉.H₂O, could be easily removed by rinsing with water, but the other, Ti-phosphate, remained on the surface. Indeed, XRD analysis of the rinsed foil, which had a dull purplish gray color, showed peaks only for Ti-phosphate, which were identical to those of powdered H₂TiPO₄. There is no long range order to the Ti-phosphate coating, and profilimetry of the surface (at 5mm/s with 5 mg force) showed rough surfaces. The resistance of Ti-phosphate to removal from Ti by rinsing of “peeling” with Scotch® tape was verified by XRD analysis; the change in relative intensities of XRD peaks for Ti-phosphate on the Ti substrate were measured before and after these tests was inconsequential. Since there is no preferred orientation for Ti-phosphate on the Ti substrate, phosphate group-derived hydroxyls of Ti-phosphate are likely also randomly oriented. The hydroxyl groups of the present invention phosphate coatings are available for further chemical modification (derivatizing), and may be reacted with, for example, hydrolytically reactive reagents, as described above for the phosphonate layers having reactive substituents. As with the phosphonate coating, further reaction of the phosphate hydroxyl moieties results in dense coverage of the surface by the derivatizing species. In this manner, species which would only provide a sparse coating on the native oxide if reacted directly can be used to provide a much denser coating on the phosphate derivatized surface.

Aqueous phosphoric acid solutions having a concentration up to about 3.0 M are preferred. For preparation of phosphate coatings of the present invention, phosphoric acid solutions having a pH more acidic than about pH 3.0 are preferred. Although these preferred ranges are convenient for providing coatings of the present invention, values outside of this range may be employed when reactivity and solubility considerations permit.

The concentration of phosphonic acid required to form an inorganic phosphate coating on an oxide surface is that concentration of phosphoric acid effective to form a stable film on the substrate surface without excessively dissolving the substrate. This can readily be determined by those of ordinary skill in the art without undue experimentation.

As with the coatings of phosphonate containing hydroxyl substituents, the hydroxyl groups of the Ti-phosphate coatings of the present invention can also serve as reactive sites for covalent attachment of hydrolytically reactive reagents, for example, Zr or Si alkoxides. It is observed, by comparison of infrared absorbance by a characteristic feature of a surface bound moiety, that surface loadings of these organometallics are 1-2 orders of magnitude higher on Ti-phosphate coatings than those obtained on the native oxide of Ti in which only about 15% of surface oxygen is derived form hydroxyl groups.

Alkyl amines and silanes are reagents commonly used to couple functionalized organics to a variety of hydroxylated surfaces, and bond readily to the phosphate surfaces of the present invention. For example, octadecyl(triethoxy)silane reacts irreversibly with Ti-phosphate but not with the Ti native oxide surface under comparable conditions. The phosphate surfaces of the present invention may be further derivatized by reagents typically used to react with hydroxylated oxide surfaces of non-titanium materials.

As described above, the native oxide surface of titanium materials is not amenable to profound alteration of the chemical properties of the surface using typical derivatizing reactions. In addition, as described above, the coverage of hydroxyl groups on a native oxide surface of titanium materials is sparse, thus, derivatizing reagents which react with hydroxyl groups (hydrolytically reactive reagents) typically yield a coverage by the derivatizing species which is too sparse to provide for a significant change in the behavior of the surface of the material. This is particularly problematic with respect to attempts to alter the native oxide surface of titanium materials with these reagents to promote adhesion when the materials are placed in contact with bone tissue.

The phosphate or phosphonate coatings of the present invention provide a layer which is sufficiently adherent and provides dense-coverage of a reactive surface directly bonded to the native oxide surface of titanium materials. Studies indicate that coverage yielded by reacting phosphate coating hydroxyl groups of the present invention with derivatizing reagents yield coverage of the oxide surface that is about one to two orders of magnitude greater than that obtainable by direct reaction of the derivatizing reagent with the surface hydroxyl groups of the native oxide surface. These dense-coverage, adherent phosphate or phosphonate coatings also can promote the adhesion of bone tissue, and are amenable for further derivatization by chemical species which further promote adhesion of various coatings. For example, the surface can be provided with a linking segment which includes a bioactive moiety that promotes the adhesion and proliferation of osteoblasts. Owing to the increase in specific surface density of reactive sites afforded by the omega-functionalized phosphonic acid-based coating layer over the density of reactive sites available on the native metal oxide surface, increased interaction between the surface of the present development and tissue contacted to the surface is observed.

The use of omega-functionalized phosphonic acid, for example, 1,6 diphosphono-hexane (a bis-phosphonic acid, with phosphonate groups terminating either end of a 6 carbon alkyl chain) and 1, 12 diphosphono-dodecane (a bis-phosphonic acid with phosphonate groups terminating either end of a 12 carbon alkyl chain), to apply a coating adhered to the native oxide surface of a material provides a layer which can be the basis of a segmented coating described above. Such coatings can be formed by stepwise reaction of the omega-functional group with a linking moiety, for example, a metal alkoxide, for example the Zr, Si, Ti, and Ca alkoxides described above, to provide a segmented coating having a bisphosphonate segment bonded to a native oxide surface and a metal oxide linking segment bonded to the bisphosphonate segment.

When the metal alkoxide segment contains hydrolyzable ligands, for example, zirconium-tetrakis-(tertiarybutoxide), one or more tert.-butoxide ligands remain after surface attachment. These ligands can be hydrolyzed to provide metal hydroxyl sites, or which can be reacted with, for example, an organic acid, providing a bonded acid. The organic moiety thus attached can in turn be used to attach other moieties, for example, bioactive moieties.

An example of this synthetic scheme is bonding a difunctional acid to a metal alkoxide linking segment, for example, attachment of maleimidobutyric acid (which contains carboxylic acid functionality terminating one end of a four carbon chain and a maleimide nitrogen terminating the other end). Attachment of the maleimide functional group using this synthetic scheme proceeds rapidly, essentially upon contact, and the maleimide functional end can be employed to further bind bioactive proteins and peptides, for example, those which promote the attachment of osteoblasts to the surface, thus providing a surface which promotes bone tissue adhesion.

An example such a surface is the surface of an implant which has been functionalized with a peptide, for example, RGDC (the cysteine modified fibronectin cell attachment peptide argynine-glycine-aspartic acid). Although the reaction between the peptide and the maleimide linking segment goes to completion, the reaction rate for the coupling reaction is slow, taking several days to run to completion at room temperature.

Additional examples of the peptides which can be attached using this synthetic scheme include KRSR (lysine-arginine-serine-arginine, which is specific for osteoblast attachment) in the form of derivatives, for example KRSRGGE and KRSRGGC (the glycine-glycine-glutamic acid and glycine-glycine-cysteine modified derivatives respectively of KRSR).

Additional examples of bioactive moieties which can be attached to a surface using this scheme include biodegradable polymers, for example, polylactide (-[-CH₂C(O)—O—]—)_(n) and polyglycolic acid (—[—CH(CH₃)C(O)—O—]—)_(n) which can be attached through strong coordinate bonds of the acid terminal groups to the zirconium metal center in a surface layer having a zirconium alkoxide linking segment. It is know to incorporate bioactive molecules, for example lactam antibiotics and growth factor-releasing hormones into such polymers. An implantable surface containing polymers of this type would provide antibiotics or hormones at the site of implantation which might be advantageous in promoting healing of the surgical site about an implanted material. It will be appreciated that these polymers can also be used as a linking segment, the functional groups of the polymer coordinating by hydrogen bonding to the omega-functional group of the surface layer formed from an omega-functionalized phosphonic acid. In this sense, the biodegradable polymers provide the linking segment, attaching the bioactive material copolymerized with the degradable polymer to the surface. Additional reactions which can be carried out with an alkoxide linking segment include the stepwise provision of layers of new materials on a surface through sequential solution reactions. This synthetic scheme can be illustrated by growth of a hydroxyapatite (Ca₁₀(PO₄)₆OH₂) surface on the above-described coating layer which has been provided with a calcium alkoxide linking segment. A hydroxyapatite material can be formed by reacting the coating layer surface alternately with phosphoric acid (H₃PO₄) and then an aqueous calcium ion source, for example, CaCl₂, CaNO₃. It will be understood that there numerous other reactions are possible.

It will be appreciated that any of the omega-functionalized phosphonic acid moieties described above will provide a surface which can be reacted with numerous other polymers and oligomers, for example, those traditionally used to form a protective, decorative, or adhesive coating. When such linking segments are introduced into coatings of the present invention, it will be appreciated that adhesion to the underlying native oxide surface will be improved. For example, when an omega-hydroxy-organo-phosphonic acid moiety is used to form a coating layer with a native oxide surface of a material, the free hydroxyl ends can be reacted with, for example, an epoxy adhesive by, for example, condensation polymerization, thereby providing in epoxy adhesive coating which is attached to the coating layer through a specific surface area bond density that exceeds what is available by direct application of the epoxy adhesive to the underlying native oxide surface. As a result, the surface area specific bond strength between the adhesive layer and the coating layer of the present invention exceeds the surface area specific bond strength observed with direct application of the adhesive to the underlying native oxide surface. It will be appreciated that the ability of the surface of the coating layer of the present invention to provide for increased surface area specific reaction sites will improve the adhesion of numerous other coating materials, for example, acrylate polymer coating.

The phosphate coatings of the present invention are rich in free hydroxyl groups. The phosphonate coatings can be made to have hydroxyl groups by using precursor acids having hydroxyl group substituents. Each of these coating layers may be further functionalized to promote covalent attachment to bone tissue proteins, or precursors thereof, for example, by using thiol compounds of the type conventionally employed to promote adhesion between gold metal implants and bone tissue. The hydrocarbon ligands of the organopolyphosphonate coatings may likewise be functionalized at a substituent on the organic ligand portion as described above for phosphonate ligand coatings to form covalent bonds with chemical precursors of bone tissue protein or with the bone tissue protein itself.

The coatings of the present invention can be applied to essentially any implant intended for bone or dental tissue contact fabricated from a material having an oxide surface at the intended bone or cental tissue interface. Implants made of titanium and alloys thereof may be employed, as well as implants which are made of materials that can be provided with an adherent titanium or other material oxide surface. Additionally, the phosphorous-based coatings of the present invention may be applied to oxide surfaces of materials other than titanium-materials and provide similar potential for bone and coating adhesion.

The methodology of the present invention enables strong adhesion between a dental or osteopathic implant and incipient bone tissue via a network of strong chemical bonds. An implant device can be fabricated and its surface processed ex-situ to provide a composite coating on the implant surfaces that will give rise to a strong, non-fracturable bone-to-implant seal following implantation. The methodology is amenable to vapor-phase or solution-phase (aerosol spray-on or “dip coating”) chemistry and proceeds under mild conditions, especially compared to plasma or laser-induced deposition. Adhesion of the phosphorous-based surface coating has been found to exceed 40 M Pascals of shear stress.

More complex species, for example, a protein or peptide, may also be bonded via the derivatized surface of the present invention to the underlying native oxide surface of an implant. For example, bonding the fibronectin cell attachment peptide, arginine-glycine-aspartic acid (RGD), for example, in its RGDC derivative form, to a surface through an organic tether is thought to enhance the osteoconductivity of the surface by providing sites for cell attachment and spreading. As described above, conventional methods for such providing surface peptide attachment to Ti alloys are often problematic and only low yields of such attachment are possible. Using the surface bonded coating of the present development, for example, a carboxylate-functionalized phosphonate coating, a cysteine-modified fibronectin cell attachment peptide (RGDC), which is commercially available (American Peptide), affords the possibility of attachment of the peptide to a reactive site on a surface of the present invention via formation of a thiol-ether bond using the surface coating of the present invention treated with traditional organic derivatization reaction techniques. It will be appreciated that other derivatization reactions are also possible.

Examples of additional peptides which may be attached include those which show specificity for cell attachment, for example KRSR (lysine-arginine-serine-arginine). These peptides can be modified without effecting their specificity for osteoblast attachment, for example, by attaching GGE (glycerine-glycine-glutamic acid) or GGC (glycine-glycine-cysteine) sequences to improve attachment to the surface, thus KRSRGGE and KRSRGGC respectively.

EXAMPLES

Example films of phosphonates and phosphates were prepared on coupons of metal foil or on disks of metal cut from billet. As noted, samples were prepared in some cases by dip coating the coupon in a bulk solution of the coating moiety and in others by aerosol application of the solution to a surface of the coupon. Aerosol application of monofunctional phosphonic acids was carried out by dissolving the acid in tetrahydrofuran (THF) or methanol, spraying the acid solution onto the target oxide surface. As noted, aerosol application was carried out either in the ambient environment by spraying a solution of the acid from a pump-spray bottle, or with the target surface residing in a standard nitrogen charged glove box.

The solvent was allowed to evaporate from the sample either with gentle heating and/or a gas current, for example, nitrogen flowing over the surface, or left to evaporate to the ambient environment by spraying in a solution of the acid from a pump-spray bottle. Where noted, solvent evaporation was carried out in the ambient environment, or in an inert atmosphere glove box. For application of difunctional phosphonic acids, two procedures were followed. In the first procedure, a THF solution of the phosphonic acid was applied to the target oxide surface while its substrate rested in the ambient atmosphere on a hot plate to aid evaporation of the solvent. The treated oxide surface and substrate were then transferred to a 120° C. oven and annealed at oven temperature for up to 48 hours. Following removal from the oven and cooling, the derivatized surface was rinsed with dry, distilled THF to ensure only bound species remained. The residue of rinsing solvent remaining on the coupon was evaporated and the coupon surface was subjected to analysis.

In the second procedure, the substrate was placed in a vessel containing a quantity of acid solution, the solvent was evaporated with the substrate in place and the substrate was annealed in an oven to react the phosphoric acid solvent to the surface with the native oxide.

In the formation of phosphate coatings, spray or dip procedures, described above, were employed to pre-coat the native oxide surface with phosphoric acid solution. Where noted, phosphoric acid was used as either a THF or aqueous solution.

Films were analyzed using a quartz microbalance and by FTIR spectroscopy, X-ray powder diffraction spectroscopy, contact angle measurement and “peel testing”. The following procedures were used.

Quartz Crystal Microbalance (QCM)

The QCM technique allows accurate, gravimetric determination of mass changes on an electrode which is deposited on a piezoelectric quartz crystal. It is, thus, ideal to monitor surface reactions of target metals when they are used as such electrodes: the QCM oscillates at a resonant frequency which is determined by the cut and mass of the crystal, and, just as for a classical oscillator, changes in electrode mass result in changes in crystal resonant frequency. Since our experiments necessitated detaching active crystals from the QCM oscillator for extended periods of time followed by reattachment, control measurements had to be made of reference crystals which were subjected to similar handling, but without surface treatment. Up to three different reference crystals (prepared in different batches) were used as received to calibrate the QCM. Careful handling of the active and reference crystals was observed to prevent unacceptably large (>10 Hz) frequency change from the initial value, during an experimental run. To ensure that monolayer coverage (at most) occurred on Ti surface, phosphonic acid-based films were subjected to copious rinsing followed by evacuation (≦10⁻² Torr) until a constant crystal frequency was established (within experimental noise levels of ±2 Hz).

Piezoelectric quarts crystals (International Crystal Manufacturers [ICM]; AT-cut, 1000 Å Ti electrodes, 10 MHz, overtone polished, 0.201 in. electrode diameter) were used for film deposition and as references. The QCM circuitry was allowed to stabilize for 30 min. after start-up, before experimental measurements were made. In each experimental run, the fundamental frequency (f_(o)) of an unreacted crystal was measured. The crystal was then removed from its holder, aerosol sprayed (on both electrodes) with a solution of the phosphorous-based acid and heated at 120° C. for 3 days. A new frequency (f_(c)) was then measured. The crystal was then subjected to rinsing followed by evacuation (≦10⁻² Torr) until a constant frequency was measured (±2 Hz), assumed to be a monolayer coverage of the Ti electrodes. The difference between the monolayer-loaded and the unreacted crystal was then related to the amount of material chemisorbed on the Ti electrode active area.

The quartz crystal microbalance (QCM) was driven by a home-built Clapp oscillator and powered by a Hewlett Packard 6234A Dual Output Power Supply. The frequency of the crystal was measured using a Hewlett Packard 5334B Universal Counter and a record of the frequencies was tracked using a laboratory computer. A change in the observed frequency indicated a change in the mass of the crystal. To ensure that all the frequency changes were attributable to the deposition of the reactants, the frequency of the crystal was monitored before and after exposure to reactants.

X-ray Powder Diffraction

Samples were analyzed by X-ray diffraction using a Rigaku Miniflex spectrometer with CuK∝ radiation and a Zn filter. Samples were scanned for 2θ=8-55° (0.04°/2 sec). Data were analyzed and refined and matched with that of known species using Jade 3.0 Pattern Processing for Windows. Samples were placed on glass microscope slides using Dow Corning Vacuum Grease, and were placed in an appropriate holder.

Infrared Spectroscopy

Samples were analyzed using either a Nicolet 730 FT-IR equipped with a Spectra Tech diffuse reflectance (DRIFT) attachment or a MIDAC Illuminator equipped with a Surface Optics specular reflectance head. When the Nicolet was used for analysis, infrared experiments were performed using a glancing angle attachment, a Variable Angle Specular Reflectance Model 500, obtained from Spectra Tech. The angle between the surface normal and the incident beam was approximately 87°. For both instruments, samples were purged with nitrogen for half an hour to reduce the amount of water on the surface, and 1,000 scans were collected to obtain a reasonable signal to noise ratio. All spectra obtained were ratioed against a spectrum of a clean native oxide surface.

“Peel-Testing”

Coupons which had been treated were rinsed several times with deposition solvent and, where appropriate, ethanol and/or water, to remove soluble residues. A piece of tape (e.g. 3M red Scotch® “650” tape or Scotch Masking Tape #234; 37 oz/in adhesion to steel) was adhered to the derivatized surface of the solvent washed foil sample and quickly removed. The freshly “peeled” coupon was then analyzed again by DRIFT spectroscopy.

Contact Angle Measurement

Contact angles were measured at room temperature and ambient conditions on a Tantec Contact Angle Meter CAM-F1.

All reagents were obtained from Aldrich Chemical unless otherwise noted. Propionic acid (99+percent), octanoic acid (99.5+percent), and stearic acid (99.5+percent) were used as received, 11-phosphonoundecanoic acid (an 11 carbon atom, linear difunctional phosphonic acid with an w-carboxylic acid functional group to the phosphonic acid) 11-hydroxy-undecylphosphonic acid (a linear, 11 carbon atom difunctional phosphonic acid having an ω-hydroxyl functional group to the phosphonic acid) were synthesized by a published procedure. Tetra(tert-butoxy) zirconium (TBZ) was distilled at 10⁻¹ torr and 80° C. The distilled product was stored in a nitrogen dry box, in the dark, and at −40° C. until needed. Otherwise, solvents were used as purchased. Titanium (0.25 mm; 99.6%), aluminum (0.25 mm; 99.0%); and iron (0.125 mm; 99.5%) foils and titanium Ti-6Al-4V billet (all obtained from Goodfellow, Inc.) were prepared for use by sanding, followed by cleaning with methanol, and cut into ca. 1 cm×1 cm coupons (foils) or 1 inch diameter disks (billet). The coupons were dried for at least an hour before use, and stored in an oven at 200° C.

The first set of comparative examples demonstrate the films which can be formed on various native metal oxide surfaces using ambient temperature contact of the surface with a carboxylic and a phosphonic acid, both of which represent classes of art-recognized oxide surface derivatizing agents.

COMPARATIVE EXAMPLES Comparative Example 1

Carboxylic Acid Treatment of Aluminum Native Oxide

A coupon of aluminum was prepared as described above. A 1.0 mM solution of stearic acid in iso-octane was prepared for deposition on the aluminum coupon. Deposition was carried out by immersing the aluminum coupon into the stearic acid solution for 24 hours, then washed with fresh iso-octane. The presence of a stearic acid film was confirmed by IR spectroscopy. The self-assembled monolayer alignments were confirmed by contact angle measurements. Washing the substrates after they were immersed in the carboxylic acid solutions aided in the removal of molecules that were not bound to the aluminum, but were merely sitting on the surface.

The films formed in solution were stable. The stearic acid film, which formed in 24 hours, was removed by anhydrous ethyl ether under mild conditions in the same amount of time. The monolayer-coated aluminum substrate was placed in ether at room temperature without using any stirring device. Removal of a significant portion of the film within 90 minutes was confirmed by IR spectroscopy. After removing the monolayer, it was possible to establish another monolayer on the aluminum surface by repeating the same technique. This could be done repeatedly, but there was a gradual erosion of the aluminum substrate.

From the IR information, it was apparent that the interaction between the carboxylic acid and the metal oxide substrate surface was weak, as illustrated by the ability to produce and remove the monolayer under mild conditions. The nature of the interaction is apparently hydrogen bonding between the acid and the hydroxyls on the surface of the metal. Apparently, covalent bonds are not formed because, if they were, much more vigorous conditions would be required to remove the carboxylic acid from the surface of the metal oxide.

Comparative Examples 2-4

Ambient Phosphonic Acid Treatment of Aluminum, Iron, and Titanium Native Oxide Surfaces

Samples of coupons of aluminum, iron, and titanium, prepared as described above, were treated with an aerosol of n-octadecanephosphonic acid in tetrahydrofuron (THF) at room temperature in the ambient environment. Following the spray application of the acid solution the solvent was allowed to evaporate at ambient temperature and the derivatized surfaces of the coupons were analyzed by FTIR. The surfaces where then washed with THF and analyzed both before and after a peel test using red Scotch® “650” tape. The analysis shows that on iron, the phosphonic acid forms a layer on the native surface oxide that, while of sparse coverage, survives both washing and peel testing. In the case of the aluminum samples, a weakly bound phosphonic acid layer is formed that survives washing, but not peel testing. For the titanium sample, any phosphonic acid which absorbed to the surface was readily removed by washing with the deposition solvent.

Comparative Examples 5

Vacuum-Anneling of Phosphonic Acid Coating Applied to Titanium Native Oxide Surfaces

A titanium coupon, prepared as described above was treated with a 0.8 mM THF solution of octadecanephosphonic acid in the form of an aerosol spray under dry N₂. The treated coupon was placed under vacuum (10⁻¹ torr), and sealed off. The coupon remained in the evacuated vessel for six hours. DRIFT analysis before and after rinsing of the sample demonstrated that none of the phosphonic acid remained on the surface after rinsing in THF.

The next group of examples demonstrates derivatization of titanium oxide surfaces according to the present invention using a phosphonic acid and phosphonic acid derivatives.

Example 1

Formation of a Bound Phosphonic Acid Film on a Titanium Native Oxide Surface

A titanium coupon, prepared as described above was treated with a 0.6 mM THF solution of octadecanephosphonic acid in the form of an aerosol spray under dry N₂. The treated coupon was left under a current of dry nitrogen until the solvent evaporated. Following solvent evaporation the sample was heated for 18 hours at 110° C. in air. The coupon was cooled to ambient temperature and rinsed twice with THF. This cycle of application, heat annealing, and rinsing was repeated five times. DRIFT analysis of the resulting coating on the coupon demonstrated that a phosphonate surface coating was bonded to the surface and remained after rinsing and peel testing. The coupons thus prepared were stored in an oven at 200° C. there being no upper limit on annealing time.

Example 2

Formation of a Difunctional, Bound Phosphonic Acid Film on a Titanium Native Oxide Surface

A 5 mM solution of 11-phosphonoundecanoic acid in dry, distilled THF was aerosol sprayed onto a titanium coupon prepared as described above using the procedure described above for preparation of films using difunctional phosphonic acids. Analysis by infrared spectroscopy (IR) of the resulting surface films produced show the characteristic IR stretches observed for alkyl chains and for bound phosphonic acids, indicating that the phosphonate group was bound to the surface of the coupon and the ω-carboxylic acid groups were oriented away from the surface and hydrogen bonded.

Example 3

Formation of a Difunctional, Bound Hydroxy-Phosphonic Acid Film on a Titanium Native Oxide Surface

A 10 mM THF solution of 11-hydroxyundecylphosphonic acid was applied to a titanium coupon, prepared as described above, as an aerosol using the procedure described for Example 2, except that baking of the sample was limited to 18 hours post application. Infrared analysis indicated that the phosphonic acid portion of the coating precursor was bound to the native oxide and showed a broad peak between 3300-3600 cm⁻¹ indicative of hydrogen bonded hydroxyl groups as well as characteristic peaks for the aliphatic chain.

Example 4

Formation of Bound, Mixed-Difunctional Phosphonic Acid Coating on a Titanium Native Oxide Surface

Using the procedure described for Example 2, above, coatings comprising mixtures of 11-phosphonoundecanate acid and either 4-phosphonobutyrate, decanephosphonate or a mixture of these species in any ratio will be prepared by aerosol applications of a solution containing a mixture of these species. The ratio of surface bound materials will be found to be close to that of the ratio of acid constituents of the solution applied. Subsequent coupling chemistry (with, for example, a phenol or an amino acid) can be accomplished to optimize yields of elaborated surface films by controlling the microenvironments of the ω-carboxlic acid termini in this manner. Similar experiments can be done for mixtures containing ω-hydroxyalkylphosphonate as well.

In the second and third groups of examples, following, films formed on titanium metal coupons using difunctional phosphonic acids (both the ω-carboxylic acid and ω-hydroxyl functional films) are further reacted with moieties useful in demonstrating the reactivity of the layer and with other moieties which are useful in the promotion of bone adhesion.

Examples 5-6

Further Derivatization of Titanium Oxide Surface Bound ω-Difunctional 11-Undecanoic Phosphonic Acid

In this second group of examples, the free carboxylic acid portion of the difunctional phosphonate layer applied to the surface of a titanium coupon prepared according to Example 2 is further reacted at the carboxylic acid site by esterification of the acid with a phenol, an amino-acid, and with a peptide.

Example 5

Formation of Amino Acid Amides of Bound ω-difunctional 11 -Undecanoic Phosphonic Acid Coating on a Titanium Native Oxide Surface

Coupons were derivatized with a carbodiimide/hydroxysuccinimide coupling reagent. Coupons prepared according to Example 2 were stirred in an aqueous solution (75 mM) of 1-ethyl-3-(3-dimethyl-aminopropyl) carbodiimide and 20 mM N-hydroxysuccinimide to form the imido adduct of the acid. The coupons thus treated were then transferred to a beaker of a 75 mM solution of lysine in water. The coupons were then extensively rinsed with water and dried under vacuum. FTIR analysis indicates the presence of an amide (coupling of the carboxylic acid of the phosphonate and the amine functional group of the lysine amino acid).

Example 6

Formation of Peptide Thio-esters of Bound ω-difunctional 11 -Undecanoic Phosphonic Acid Coating on a Titanium Native Oxide Surface

The use of a surface of the present invention to bind short peptides to a Ti or alloy surface is demonstrated next. A cysteine-modified peptide, RGDC (Arg-Gly-Asp-Cys), described above which occurs in Firbronectin cell-adhesive protein, is selected for attachment to the carboxylic acid ends of surface layers on titanium coupons prepared according to Example 2, above. The coupons are first treated with a solution of dicyclohexylcarbodiimide and N-(6-hydroxyhexyl)maleimide in dichloromethane to provide the ω-carboxylic acid groups of the derivatized surface of the coupon with a maleimide ester group that will react with thiol functionality in the cysteine of the modified peptide. Foils are then bathed in an aqueous solution of RGDC (Arg-Gly-Asp-Cys) to couple the thiol group of cysteine to the immobilized maleimide group, leading to the attachment of RGDC to the ω-carboxylic acid-maleimide, yielding a bioactivated Ti surface.

In this second group of examples, the free hydroxide portion of the difunctional phosphonate layer applied to the surface of a titanium coupon prepared according to Example 3 using 11-hydroxy-undecylphosphonic acid is further reacted at the hydroxy functional group by conventional organic chemistry with dansyl chloride, an amino-acid, and with a peptide

Example 7

Reaction of Titanium Oxide Surface Bound ω-Difunctional 11-Hydroxy-Undecyl Phosphonic Acid With Dansyl Chloride

Titanium coupons prepared according to Example 3 above were placed in a solution of approximately 10 mg of dansyl chloride and 0.1 mL of triethylamine in 10 mL of acetonitrile. The solution was stirred for 18 hours under N₂. Coupons were removed from the solution, blotted dry and rinsed with acetonitrile. The coupons were then subjected to FTIR analysis which indicates, by the presence of new peaks at 1600 cm⁻¹ and at 1200-1100 cm⁻¹, that a sulfonate ester formed. The dansyl adduct has a characteristic fluorescence spectrum, and fluorescence microscopic analysis of the coupons confirms the formation of the surface-bound dansyl ester product. The fluorescence spectroscopy also indicates that the coating is dense-coverage and uniform over the entire surface of the coupon.

For the next two examples, the surface bound hydroxyphosphonate is converted into the maleimide adduct according to the following procedure. A coupon prepared according to Example 3, above, is placed into a solution of about 15 mg of 3-maleimido-(propionic-acid-N-hydroxysuccinimide) ester in 10 mL of acetonitrile. The coupon is then transferred into a nitrogen glove box and placed into an ambient temperature maleimide solution for 24-72 hrs, after which, coupons are removed from the solution and blotted dry, and rinsed with acetonitrile. FTIR analysis indicates peaks corresponding to 11-hydroxyundecylphosphonate bound to the surface of the coupon through the phosphonate functional group, with additional peaks at 1731 and 1707 cm⁻¹ corresponding to the carbonyl stretches of the maleimide adduct.

Examples 8

Reaction of Titanium Oxide Surface Bound ω-Difunctional 11 -Hydroxy-Undecyl Phosphonic Acid With Cysteine

Coupons having the phosphonate-maleimide adduct, prepared as described above on titanium coupons prepared according to Example 3, were placed in a stirred solution of 15 mg. of cysteine dissolved in 10 mL of doubly distilled, Millipore™-filtered water for 8-24 hrs. The foils were removed from solution, dried, and rinsed in doubly distilled water. FTIR analysis of the coupons showed changes in the maleimide carbonyl region and a new peak at ca. 1700 cm⁻¹, indicative of the presence of cysteine bound to the coupon.

Examples 9

Reaction of Titanium Oxide Surface Bound ω-Difunctional 11-Hydroxy-Undecyl Phosphonic Acid With a Peptide

Coupons containing the phosphoric coated-maleimide adduct, prepared as described above from titanium coupons prepared according to Example 3, are placed in a solution of the peptide RGDC (Arg-Gly-Asp-Cys) used to prepare coupons of Example 7, above. The RGDC solution comprises about 10 mg of the peptide in 10 mL of doubly distilled, Millipore™-filtered water. Coupons are stirred at ambient temperature for about 8 to about 48 hours. The coupons are removed from solution, dried, and rinsed in doubly distilled water. FTIR, analysis before and after peptide treatment demonstrates changes in the maleimide carbonyl region and broadening in the carboxylate region (^(˜)1700 cm⁻) which persists after two solvent rinses, indicating the presence of the RGDC tetrapeptide bound to the coupons.

It will be appreciated that peptides and amino acids can be “tagged” with a fluorescent marker by covalent bonding a small fluorescent species, such as dansyl chloride as an ester or thioester to the parent compound. It will be appreciated that amino acids and peptides which are bound to phosphonate species bonded to oxide surfaces, such as are described above can be tagged before or after such bonding reactions. When the surface species amino acid and peptide adducts are “tagged” in this manner, examination of the coupons by fluorescence microscopy after derivitization indicates the coatings of the peptide bounded to the coupon are dense and uniform over the entire coupon.

The next group of examples demonstrates the dense-coverage of a titanium native oxide surface that can be achieved with the coating of the present invention.

Examples 10-11

Formations of a Phosphonate Coating on a Titanium Quartz Microbalance Electrode

As described above, quartz microbance electrodes were treated with octylphosphonic acid and 11-hydroxyundecylphosphonic acid to form an octylphosphonate and undecylphosphonate coating on the native oxide layer on the electrodes, the results of microbalance measurement of the density of surface coverage for the two species is presented below in Table I.

TABLE 1 Surface coverage of Ti by alkylphosphonates. Phosphonate Δf(Hz) Coverage (nmol/cm²)^(a,b) Octylphosphonate 109 2.46 (1.89) 115 2.60 (2.0) 11-Hydroxyundecylphosphonate 141 2.46 (1.89) 165 2.87 (2.21) 115 2.00 (2.21 140 2.44 (1.88) ^(a)As measured by QCM ^(b)Corrected value for surface roughness factor measured to be 1.3 by AFM analysis of the sputtered Ti electrode given in ( ).

Example 12

Atomic Force Microscopy of an Octadecylphosphonate Coating

A coating of octadecylphosphonate on the native oxide surface of a polished titanium coupon was prepared by the, aerosol method described above using a 0.75 mM THF solution of octadecylphosphonic acid. The acid solution was applied under nitrogen and evaporated using the ambient method. The spray-heat-rinse cycle was repeated 6 times. The resultant coating was studied by atomic force microscopy (AFM) using a Dimension 3000 (Digital Instruments) operated in “soft” TappingMode. An AFM micrograph of the polished Ti foil surface shows it to have grooves (resulting from the polishing process), but regions between these grooves are appreciably flat (mean roughness ≈0.7 nm; FIG. 3). Section analyses examined surface roughness in more detail. The morphology of the surface changed dramatically on formation of the octadecylphosphonic acid film. On coated coupons, AFM micrograph and section analysis showed islands (typical diameter ≈50 nm) of similar height (≈2.2 nm), consistent with monolayer formation on the surface, and the mean roughness of the surface increased to 1.5 nm on monolayer attachment. With reference to film height data obtained for a self-assembled monolayer of this same phosphonic acid on mica (≈1.8 nm), an alkyl chain tilt angle of about 33° was estimated. The AFM analysis indicates the coating is of dense-coverage. Correction of the microbalance results of Examples 10 and 11 by the AFM data indicate a surface coverage in excess of 20 times of that observed for reactions of the native oxide hydroxyl sites, described above.

The next example demonstrates the use of a functionalized alkyl-phosphonate coating of the present invention to bond a bone-growth promoting peptide RGDC (described above) to the surface of a titanium alloy (Ti-6Al-4V), and the use of this derivatized surface in adhering and proliferating osteoblasts.

Example 13

Application of a Phosphonate Coating to a Titanium Alloy and Subsequent Peptide Derivatization to Provide an Osteoblast Adhesion Promoting Surface

Disks of Titanium Alloy Ti-6Al-4V prepared as described above were coated with a layer of 11-hydroxyundecylphosphonate by placing them in a vessel filled with a 10 mM THF solution of 11-hydroxyundecylphosphonic acid. The THF was allowed to evaporate and the disks were then baked in an oven at 120° C. for 48 hours and were rinsed in dry THF. Thus prepare the titanium alloy disks were further derivatized with the cysteine modified fibronectin cell attachment peptide argynine glycine aspartic acid (RGDC) which has been described above.

The RGDC peptide [American Peptide] was bonded to the phosphonate coating using a maleimide coupling procedure. The maleimide derivative of the hydroxy functionalized phosphonate coating was prepared by placing the coated disk into a 5 mM acetonitrile solution of 3-maleimidopropionic acid-N-hydroxysuccinimide ester for a period of 24 hours at room temperature. Thus prepared the maleimide adduct was rinsed with a fresh acetonitrile solution. The disks were transferred into an acetonitrile solution of the peptide described above, RGDC, with stirring for 24 hours, yielding the peptide bound via a thiol-ether linkage through the cysteine residue to the hydroxy end of the phosphonate coating.

These modified titanium alloy disks were examined for their interaction with human osteoblasts. Human fetal osteoblasts (HFOB 1.19; ATCC) were maintained in a 1:1 mixture of Ham's F12 and Dulbecco's modified Eagle's medium (DMEM), without phenol red (GIBCO, BRL), 10% fetal bovine serum (Hyclone Laboratories) and 0.3 mg/ml G418 (GIBCO, BRL). Cells were labeled with 10 μM Cell Tracker Orange (Molecular Probes, OR) for 30 minutes at 34° C. After this time, the medium was removed and replaced with fresh medium and serum for an additional 30 minutes at 34° C. Cells were released from tissue culture dishes using 0.2 mg/ml EDTA in PBS, washed with PBS, re-suspended in serum-free medium at 1×10⁵/ml, and 500 μL of the cell suspension was added to wells containing the metal disk substrates which had been blocked with 1% BSA in PBS for 30 minutes before cell addition. Cells were allowed to spread on the substrates for 90 minutes, after which time they are washed with PBS and visualized using a Nikon Optiphot-2 microscope. Images were captured using a Photometrics Coolsnap camera and analyzed using Coolsnap and IP labs software.

The results of this study indicate that human osteoblasts can adhere and propagate on surfaces prepared according to the present invention.

Examples 1-12 were duplicated by treating coupons made from titanium alloy Ti-6Al-4V (Goodfellow) under the same conditions and with the same reagents used for the titanium coupons used in Examples 1-12. Results were the same, demonstrating that the coatings of the present invention can be applied equally well to the native oxide of titanium alloys using the methods of the present invention.

The next group of examples demonstrates the use of phosphoric acid to form an intermediate layer on titanium metal native oxide surfaces which may be further derivatized with other moieties, and a derivatized surface which can promote osteoblast adhesion and spreading.

Examples 14-15

Dip-Treatment of Titanium Native Oxide Surfaces in Phosphoric Acid Solution

In Example 14, a coupon of Titanium foil (99.6+ % annealed), prepared as described above, was immersed in 1.4M aqueous H₃PO₄ (pH=1.5) at room temperature for one hour, then heated at 110° C. for greater than 16 hours. After two rinsings with THF, examination by DRIFTS showed that it had a coating of Ti(H₂PO₄)₃ (hereinafter Ti-phosphate) remained that could not be rinsed away.

In Example 15, titanium coupons prepared and described above were dipped in an aqueous solution of phosphoric acid (1.45 m; pH 1.5) for 1 hr at ambient temperature an pressure. The coupons were then removed from solution and warmed in an oven at 120° C. for 18 hrs., then cooled, rinsed with water, and “peeled” with masking tape to remove any weakly adsorbed material. X-ray powder diffraction analysis and Diffuse Reflectance Fourier Transform Infrared analysis (DRIFT) confirmed the presence of phosphate coating (Ti-phosphate).

Coated coupons were prepared in accordance with Example 15 and further derivatized using the spray/heat/rinse procedure described above using the reagents indicated below in Table II.

TABLE II Solute concentration/ Baking Example Derivatizing species solvent temperature/time 16 octadecyl(triethoxy) 1.8 mM/THF 120° C./24 hrs. silane 17 octadecanethiol 1.0 mM/THF  60° C./24 hrs. 18 octadecylamine 1.0 mM/THF  60° C./18 hrs. 19 octadecyl(triethoxy)- 0.8 mM/THF 120° C./16 hrs. silane

In each case, adherent, dense-coverage coatings of the reactant found on the surface of the phosphate coated coupon by IR analysis.

Example 20

Treatment of Phosphate Coatings With Hydrolytically Reactive Metal Alkoxides

Coupons prepared according to Example 15 were put in a horizontal tube which could be externally cooled and which was equipped with two stopcocks for exposure to vacuum (10⁻³ Torr) or to vapor phase tetra(tert-butoxy)zirconium (Zr(O-t-but)₄). Coupons were subjected to three cycles each consisting of alternating exposure to vapor of Zr(O-t-but)₄ with external evacuation for 15 min, followed by 30 min exposure to the organometallic reagent vapor without external evacuation. The first cycle was done at room temperature, and the latter two with external cooling by dry ice. Coupons were then subjected to room temperature vacuum (10³ Torr) for 16 hrs to remove any physisorbed Zr(O-t-but)₄. DRIFT analysis confirmed formation of dense-coverage surface Zr alkoxide.

Example 21

Derivatization of a Dense-Coverage Zr Alkoxide Bound to Titanium

Coupons prepared according to Example 20 were sprayed with 1.75 mM solution of octadecylphosphonic acid in dry tetrahydrofuran (THF). Samples were evacuated overnight (0.1 Torr), rinsed with THF, “peeled,” tested and analyzed by DRIFT. The analysis demonstrated an adherent alkyl-phosphonate coating bonded to the zirconated surface.

The derivatization reactions of Examples 14 through 21 were repeated, using the same reagents and conditions on coupons of Ti-6Al-4V (Goodfellow) prepared according to the procedure described for Example 15 above. Analysis of the coatings prepared showed that titanium alloy can be derivatized in the same manner with the same results seen from the titanium.

The next group of examples demonstrates the use of a phosphate coating of the present development to provide a derivatized surface on a titanium material which promotes the adhesion and proliferation of osteoblasts.

Examples 22-23

Adhesion of Osteoblasts to a Titanium Material Phosphate Coated Peptide Derivatized Surface

Disks cut from titanium billet and from titanium alloy Ti-6Al-4V billet were prepared and coated with a phosphate coating according to Example 15.

A phosphate coated disk of each material was placed in a Teflon® well and they were each treated with a solution of amino propyl-(tri ethoxy)-silane (10 mM in THF), and then solvent rinsed, with sonication, to give surface-bound 3-amino-propyl siloxanes. These disks were then further derivatized by placing each in a 5 mM acetonitrile solution of 3-maleimidopropionic-acid-N-hydroxysuccinimide-ester for 18 hours at room temperature to give the maleimide adduct. The disks were removed from solution, solvent evaporated, and analyzed by IR. They were then rinsed in acetonitrile, with sonication, and dried in vacuo (0.1 Torr). The disks were further derivatized by placing them into a solution of the RGDC peptide used in Example 13 above, (5 mM), prepared in 5 ml of purified water (Millipore), with the pH adjusted to 6.5 using 0.1M NaOH. The disks remained in the peptide solution stirring at room temperature for 24 hours. Formation of the surface bound RGDC was verified by IR. The disks were then rinsed with water, dried, subjected to tape peel testing, and reanalyzed by IR. The peptide coating was found to be adherent.

The peptide coated disks were subjected to the human osteoblast test described above in Example 13. The results showed that the surface promoted the adhesion and proliferation of osteoblasts.

Example 24

Derivitazation of Phosphate Coating with 11-Mercaptoundecanoic Acid

Mercaptoundecanoic acid was recrystallized from ethanol at room temperature. A solution of mercaptoundecanoic acid (1.0 mM in THF) was applied by aerosol deposit onto coupons of titanium and of titanium alloy Ti-6Al-4V. The coupons were placed under N₂ for 6-12 hrs in a horizontal tube equipped with a stopcock to regulate N₂ flow and pressure, then evacuated at 0.1 Torr for at least 4 hrs, and analyzed by DRIFT. A dense coating of the mercaptan was found adhered to the surface of both the metal and alloy.

Next is presented an example of using a bisphosphonic acid to provide an adherent coating layer which is further derivatized to form a coating having a phosphonate segment and a linking segment. Additional examples are presented in which this segmented coating layer is further derivatized to provide a peptide-bearing surface, a calcium apatite surface and a mixture of peptide and calcium apatite.

Example 25

Derivatization of the Native Oxide Surface of Ti-6-Al-4-V Titanium Alloy by Formation of a Surface Coating

Layer Having a 1,6 Diphosphonohexane Segment and a Linking Segment

A coupon of Ti-6-Al-4-V titanium alloy (extra low interstitial grade ⅜″diameter rod, from Titanium Industries, Morristown, N.J.) was prepared by cutting 1 mm sections from the rod stock using an art recognized wire electric discharge cutting technique. The surface of the coupon was prepared by sanding and then successively washed with methylene chloride, 2-butanone, and then methanol. After a methanol rinse, the coupons were stored under air in an oven at 200° C.

The bisphosphonic acid was synthesized and purified according to published procedures, all other reagents were used as received. A coating layer was applied to the coupon by dropwise application of a 1.0 mM aqueous solution of the 1,6 hexane-bisphosphonic acid onto the surface of the coupon under ambient conditions and transferring the sample into a 120° C. oven in air for 48 hours. At the end of the baking period, the samples were rinsed with distilled water, sonicated in distilled water for 20 minutes (Branson 2610 Sonic Cleaner), and dried in vacuo at ambient temperature (about 0.01 mm Hg for 5 hours). The presence of a bisphonate layer was verified by infrared (IR) analysis as described above.

Preparation of a Coating Layer Having a Bisphosphonate Segment and an Alkoxide Linking Segment

The surface of the bisphosphonate coating layer on coupons, prepared as described above, was further derivatized by reaction with a zirconium alkoxide. Thus, a coupon coated as described above was placed into a vacuum deposition chamber which was fitted with a bulb containing freshly vacuum distilled zirconium tetrakis-(tert.-butoxide). The chamber was closed and evacuated to 5.5 millitorr. The chamber was sealed from the vacuum source and the bulb was opened, admitting zirconium alkoxide vapor to a pressure of about 3 millitorr for 30 minutes at ambient temperature. The chamber was again evacuated to 5.5 millitorr and the cycle repeated twice more. At the end of the third exposure to zirconium alkoxide, the sample was subjected to a vacuum of 3 millitorr for two hours. The presence of the zirconium linking segment bound to the surface coating layer was verified by IR analysis, as described above. Coupons having a segmented coating layer prepared according to this procedure were further handled in a nitrogen glove box.

Preparation of a Coating Layer Having Bound Peptide

The coupons having a coating layer comprising a bisphosphonate segment and an alkoxide segment (segmented coating layer), prepared as described above, were subjected to further derivitization reactions to bind a peptide to the zirconium alkoxide linking segment. This was accomplished by reacting the residual alkoxide moieties with a difunctional organic acid (6-maleimido-hexanoic acid, Sigma, used as received), bonding the carboxylate functional group to the zirconium. The surface bound acid was then reacted at the maleimide functional group with a peptide derivative. Thus, an anhydrous 1.0 mM tetrahydrofuran (THF) solution of the carboxylic acid was aerosol sprayed in a dry box onto the coupon prepared as described above, according to the aerosol procedure described above. The samples were subjected to a vacuum of about 0.01 torr for 12 hours, then rinsed and sonicated in THF and dried again in vacuo. The binding of the carboxylic acid species to the zirconium segment of the coating layer was verified by IR analysis, as described above. A 2 mM aqueous solution of the cysteine modified RGD peptide (RGDC) described above was adjusted to pH 6.5 with NaOH. Coupons which had been previously derivatized with 4-maleimidobutyric acid were stirred in the RGDC peptide solution at 25° C. for 24 hours.

The coupons which were derivatized with RGDC peptide were incubated with human fetal osteoblasts, as described above. These surfaces were found to promote proliferation of cell attachment.

Example 26

Preparation of a Coating Layer Having a “Patterned” Alkoxide Linking Segment Surface

It will be found that application of a small droplet of a solution of zirconium-tetrakis-(tert.-butoxide) (prepared as described above in Example 25) to the surface of a coating layer prepared from 1,6 hexanediphosphonic acid in accordance with the process described in Example 25 will provide a zirconium alkoxide linking segment confined to the area of the surface contacted by the droplet. By applying small droplets to the surface in selected areas it will be found that subsequent treatment of the surface with 6-maleimido-hexanoic acid in accordance with the procedure described for Example 25 will provide bonding of the carboxylic acid to the surface only in those areas which were contacted by the zirconium alkoxide. It will be found that subsequent treatment of the surface with RGDC peptide according to the procedure described above in Example 25 will yield a surface which has a “pattern” of the peptide bound to the surface only in those areas of the surface having the zirconium alkoxide linking segment.

It will be appreciated that the surface can be provided with a “pattern” using the process described in Example 26 by contacting the surface with a solution of the zirconium alkoxide through a “mask”, or by direct application of a solution to the surface in a pattern, or by any of the known techniques for application of a pattern, for example, by “inkjet” printing or by “screen” printing.

Example 27

Formation of Calcium Hydroxy-Apatite Surface

It will be found that when the bisphonate coating layer prepared as described in Example 25 is subsequently reacted with a calcium alkoxide instead of a zirconium alkoxide, there is provided a segmented coating layer having a bisphosphonate segment bonded to the native surface oxide layer and a calcium alkoxide linking segment bonded to the bisphosphonate segment (hereafter, calcium-functionalized coating layer). It will also be found that a calcium-functionalized coating layer provides a surface upon which a synthetic calcium apatite surface can be formed by sequentially reacting the calcium-functionalized coating layer with phosphoric acid and a calcium alkoxide reagent. Thus, by substituting calcium-bis(2-methoxy-ethoxide) for tetrakis-zirconium-(tert.-butoxide) in the procedure described above for the preparation of a coating layer having a zirconium alkoxide linking segment (Example 25), a segmented coating layer having bisphosphonate segment bonded to the native oxide layer of a titanium coupon and a calcium alkoxide segment bonded to the bisphosphonate segment will be prepared.

It will be found that by reacting the calcium alkoxide functionalized coating thus prepared with an aqueous solution of phosphoric acid, a calcium-hydroxy-phosphate surface is prepared. It will be found that by alternatively reacting the surface thus prepared with additional amounts of calcium-bis-(2-methoxy-ethoxide) and phosphoric acid, a calcium hydroxy-phosphate surface layer of suitable thickness to permit growth of an adherent layer of hydroxyapatite on the surface using known sol-gel processing techniques is provided.

Example 28

Preparation of “Mixed” Pattern Surfaces

It will be found that a coating layer prepared from treatment of a titanium coupon with a solution of 1,6 hexane-diphosphonic acid according to the process described in Example 25 can be provided with a pattern comprising interspersed regions of osteoblast adhesion-promoting peptides and hydroxyapatite by patterning the surface first with a peptide that promotes osteoblast adhesion using the process described in Example 26 to pattern the surface with zirconium linking segments, attaching to the zirconium linking segments 6-maleimido-hexanoic acid according to the process described in Example 25, and then further derivatizing the surface of the coating layer with a calcium alkoxide linking segment in the areas not receiving a zirconium alkoxide linking segment by reacting the surface with a solution of calcium bis-(2-methoxy-ethoxide) according to the procedure described in Example 27. It will be found that such a surface will promote osteoblast adhesion and bone tissue infiltration into the surface when the surface is placed into contact with living bone tissue.

Example 29

A Phosphonate/Epoxide Segmented Coating Layer

Titanium coupons having a coating prepared according to Example 3 above (a phosphonate coating derived from 11-hydroxy-undecyl phosphonic acid) were further derivatized with an epoxy linking group by applying a film of Cytec Fiberite FM 1000® epoxy adhesive to the surface. Before the adhesive cured, a second titanium coupon prepared according to Example 3 was placed in contact with the epoxy such that a lap joint was formed having a 284 mm² area. The epoxy was permitted to dry under ambient conditions. Additional examples were prepared from titanium metal coupons having a sanded, washed, and baked surface, as described above, but without a phosphonate coating. The strength of the joint between the coupons for the coated and uncoated samples was tested according to ASTM testing standard F1044-99. It was found that on average, the joint between the uncoated coupons failed at 40 MPa and between the coated coupons, the joint failed on average at about 60 MPa of applied pressure.

Example 30

Direct Deposition of Octadeclyphosphonic Acid (ODPA) on Titanium

A 0.8 mM TIff solution of ODFA in the form of an aerosol spray under dry N2 was deposited on titanium foil (99.6+% annealed) under vacuum (10⁻¹ torr), which was maintained with the pump off for six hours.

The coating was completely washed away with one rinse.

A 0.6 mM TI-IF solution of ODPA was sprayed under dry N² on titanium foil (99.6+% annealed). Following solvent evaporation the sample was heated for 18 hours at 100° C. and rinsed twice with ThF.

Repeating the spray-heat-rinse cycle five times prod Liced a durable coating that did not wash away.

Direct Deposition of Phosphoric Acid on Titanium

Titanium foil (99.6+% annealed) was immersed in 1.4M aqueous H₃P0 ₄ (pH=1.5) at room temperature for one hour, then heated at 110° C. for greater than 16 hours. After two rinsings with THF, a coating of Ti(H₂ P0 ₄)₃ remained that could not be rinsed away.

It was discovered that immersion of cleaned titanium slides in a 1.4M H₃PO₄ bath for at least one minute, followed by oven-heating to 110° C. for at least 3 hours, was sufficient treatment to produce titanium phosphate surface compounds. A summary of the different variables tested and the effect they had on the formation of titanium phosphate surface compounds is displayed in Table I.

TABLE I Heat Time Surface Example H₃PO4 pH Soaking Time 110° C. Compound 18 1.4 M ~0.5 >1 hr. >6 hrs. Y 19 2.8 M ~0 >1 hr. >6 hrs. Y 20 0.7 M ~1 >1 hr. >6 hrs. N 21 1.4 M ~1.5 >1 hr. >6 hrs. N 22 1.4 M ~2 >1 hr. >6 hrs. N 23 1.4 M ~0.5 1 minute >6 hrs. Y 24 1.4 M ~0.5 >1 hr. >6 hrs. Y 25 1.4 M ~0.5 >1 hr. >3 hrs. N 26 1.4 M ~0.5 >1 hr. 3-24 hrs. Y 

1. An implantable device comprising a metal, metal alloy, metalloid, polymeric or ceramic surface with an oxide overlayer, and a phosphonic acid coating layer covalently bonded to the oxide overlayer, wherein said coating layer is formed by coating said oxide overlayer with a self-assembled layer of organophosphonic acid molecules comprising organic ligands containing from about 2 to 20 carbon atoms and heating said coated oxide overlayer so that the organophosphonic acid groups react with said oxide overlayer and bond said self-assembled layer thereto, and the phosphonic acid organic ligands are functionalized at the omega carbons.
 2. The implantable device of claim 1, wherein the oxide overlayer is a native oxide overlayer.
 3. The implantable device of claim 2, wherein the phosphonic acid coating layer is formed by coating the oxide overlayer with a phosphonic acid having the formula H₂RPO₃ wherein R is an omega functionalized hydrocarbon ligand.
 4. The implantable device of claim 2, wherein the device surface comprises titanium metal or an alloy thereof.
 5. The implantable device of claim 1, wherein the phosphonic acid coating layer is formed by coating the oxide overlayer with a phosphonic acid having the formula H₂RPO₃, wherein R is an omega-functionalized hydrocarbon ligand.
 6. The implantable device of claim 1, wherein the device surface comprises titanium metal or an alloy thereof.
 7. The implantable device of claim 1, wherein the device is a dental, medical or orthopedic implant.
 8. The implantable device of claim 7, wherein the orthopedic device is selected from the group consisting of knee replacement devices and hip replacement devices.
 9. The implantable device of claim 1, wherein the omega carbon is directed away from the substrate surface.
 10. The implantable device of claim 1, wherein the ligands are chemically transformed to react and covalently bond to bone protein or osteoconductive proteins or peptides.
 11. The implantable device of claim 1, wherein the phosphonates are functionalized at the omega carbon with groups selected from the groups consisting of amino, carboxylate and thiol groups.
 12. An implantable device comprising a metalloid, polymeric or ceramic surface with an oxide overlayer, and a coating layer directly contacting said surface, wherein said coating layer comprises inorganic phosphate groups and said inorganic phosphate layer is formed by coating said oxide surface with a phosphoric acid solution and heating said coated oxide overlayer so that so that said phosphoric acid coating reacts with said oxide overlayer and bonds said phosphoric acid coating thereto, thereby providing an inorganic phosphate coating comprising free hydroxyl groups.
 13. The implantable device of claim 12, wherein the inorganic phosphate layer is functionalized for covalent attachment of bone tissue proteins or osteoconductive proteins or peptides.
 14. The implantable device of claim 12, wherein the inorganic phosphate coating is covalently bonded to the oxide layer.
 15. The implantable device of claim 12, wherein the device is a dental, medical or orthopedic implant. 